Quantitative ultrasound using fundamental and harmonic signals

ABSTRACT

A system and method include control of an ultrasound system transducer to acquire an echo signal power spectrum of a region of tissue for a fundamental frequency band and an echo signal power spectrum of the region of tissue for a harmonic frequency band, wherein a center frequency of the harmonic frequency band is substantially similar to a center frequency of the fundamental frequency band, determination of a first backscatter coefficient based on the echo signal power spectrum of the region of tissue for a fundamental frequency band and an echo signal power spectrum of a reference phantom for the fundamental frequency band, determination of a value representing a second backscatter coefficient and a non-linearity term associated with the region of tissue based on the echo signal power spectrum of the region of tissue for the harmonic frequency band and an echo signal power spectrum of the reference phantom for the harmonic frequency band, determination of the non-linearity term associated with the region of tissue based on the first backscatter coefficient and the value, and display the second backscatter coefficient, the non-linearity term, and a B-mode image of the region of tissue.

CROSS-REFERENCE TO RELATED APPLICATIONS

This is a continuation application of U.S. patent application Ser. No.16/358,808, filed Mar. 20, 2019 and entitled “Quantitative UltrasoundUsing Fundamental and Harmonic Signals”, the contents of which areincorporated herein by reference for all purposes.

BACKGROUND

A conventional ultrasound imaging system creates an internal image(i.e., a B-mode image) of a volume by detecting acoustic impedancediscontinuities within the volume. More specifically, conventionalultrasound imaging involves transmitting ultrasound beams into a volumeand detecting the returned signals which reflect from acoustic impedancediscontinuities within the volume. Since different materials typicallyexhibit different acoustic impedances, the detected acoustic impedancediscontinuities represent the locations of different materials withinthe volume.

The above-described B-mode images depict qualitative features in tissuebut do not directly provide quantitative information regarding thetissue. Quantitative ultrasound systems, on the other hand, candetermine an attenuation coefficient (AC) and a backscatter coefficient(BSC) of a Region of Interest (ROI). The AC is a measure of theultrasound energy loss in tissue and the BSC is a measure of theultrasound energy returned from tissue. Quantitative ultrasound valuessuch as these are helpful in characterizing properties of tissue such asstiffness and fat fraction. Additional quantitative ultrasound measureswould further assist these characterizations.

Determination of an AC and a BSC require compensation for system effectsof the acquiring ultrasound system. These effects include transmit-pulsepower, transducer sensitivity, beam-focusing pattern, anddepth-dependent receiver gain. Conventionally, compensation includesdividing the echo signal power spectrum of a tissue sample in thefundamental frequency band by the echo signal power spectrum of awell-characterized reference phantom in the fundamental frequency bandfrom the same depth. The resulting quotient is a normalized spectrumthat depends on the attenuation and backscatter properties of the tissuesample and of the reference phantom. Since the properties of thereference phantom are known, the AC and the BSC of the tissue sample canbe derived from the normalized spectrum.

One drawback of the foregoing determination is the need to acquirereference phantom data at the time of the clinical scan. This additionalacquisition hinders workflow and patient throughput. Moreover, theaccuracy of such determinations has been seen as lacking in manyscenarios. The foregoing determination also fails to provide otherpotentially-useful quantitative measures, such as tissue non-linearity.

BRIEF DESCRIPTION OF THE DRAWINGS

The construction and usage of embodiments will become apparent fromconsideration of the following specification as illustrated in theaccompanying drawings, in which like reference numerals designate likeparts, and wherein:

FIG. 1 is a block diagram of a quantitative ultrasound system accordingto some embodiments;

FIG. 2 is a flow diagram of a process to determine quantitativeultrasound values according to some embodiments;

FIG. 3 is a block diagram of an ultrasound system to acquire referencephantom calibration data according to some embodiments;

FIG. 4 is a tabular representation of data for determining referencephantom calibration data according to some embodiments;

FIG. 5 is an ultrasound image including quantitative ultrasound valuesaccording to some embodiments; and

FIG. 6 is a block diagram of an ultrasound system according to someembodiments.

DETAILED DESCRIPTION

The following description is provided to enable any person in the art tomake and use the described embodiments and sets forth the best modecontemplated for carrying out the described embodiments. Variousmodifications, however, will remain apparent to those in the art.

Some embodiments provide efficient and accurate determination ofquantitative ultrasound values. More specifically, some embodimentsprovide an inventive system to determine an AC and a BSC based on echosignal power spectra from a harmonic frequency band. Using the harmonicfrequency band is clinically more desirable. The clinical benefit ofusing harmonic signals is improved repeatability and reproducibility ofQUS estimates from reduced reverberation, clutter noise, and phaseaberration.

Such embodiments may utilize pre-stored echo signal power spectra (or RFor IQ signal data from which power spectra may be computed) of awell-characterized reference phantom in the harmonic frequency band,eliminating the need to acquire calibration data at or near to the timeof clinical data acquisition.

Some embodiments advantageously determine quantitative values of tissuenon-linearity. In contrast, the conventional systems described aboveassume that the non-linearity of the reference phantom is substantiallyequal to the non-linearity of the tissue in the ROI.

FIG. 1 illustrates an implementation according to some embodiments.System 100 includes ultrasound unit 110, ultrasound transducer 120 anddisplay 130. Volume 140 may comprise a human body but embodiments arenot limited thereto. Ultrasound transducer 100 may comprise any suitableultrasound transducer, such as but not limited to a phased-array, linearor convex ultrasound transducer.

Generally, processing unit 112 of unit 110 may execute program code tocontrol transducer 120 to transmit ultrasound beams into volume 140 andreceive acoustic radio-frequency signals therefrom. Processing unit 112of unit 110 may execute program code to generate images and/or determinequantitative ultrasound values based on the received signals. The imagesand/or determined values may be displayed to a technician on display130.

According to some embodiments, a technician operates system 100 toacquire echo signal power spectra of a harmonic frequency band from aROI of volume 140. Acquisition may include acquiring RF or IQ signalsand computing echo signal power spectra of the harmonic frequency bandtherefrom. The acquisition is performed using first scan settings, whichmay include particular values of frequency, F-number/aperture size,focus and apodization function parameters. Transducer 120 operates inconjunction with transmission unit 116 to transmit ultrasound beams intothe ROI and receiver unit 118 operates in conjunction with transducer120 to receive reflected signals in the harmonic frequency band from theROI according to the scan settings.

Next, harmonic calibration data corresponding to the first scan settingsis retrieved from storage 114. The harmonic calibration data maycomprise an echo signal power spectrum of a harmonic frequency band (ordata from which the echo signal power spectrum may be derived) acquiredfrom a reference phantom using scan settings which are identical orsubstantially similar to the first scan settings. Acquisition andstorage of the harmonic calibration data is described in detail below.

The echo signal power spectra acquired from volume 140 is normalized bydividing the echo signal power spectra by the stored echo signal powerspectrum. The result is a normalized spectrum that depends only on theattenuation and backscatter properties of the tissues of the ROI and thereference phantom. Since the attenuation and backscatter properties ofthe reference phantom are known, the AC and the BSC of the tissues canbe derived from the normalized spectrum as will be described in detailbelow.

According to some embodiments, echo signal power spectra of afundamental frequency band is also acquired from the ROI of volume 140.The acquisition is performed using second scan settings, which maydiffer or not from the first scan settings mentioned above. Fundamentalcalibration data corresponding to the second scan settings is retrievedfrom storage 114. The fundamental calibration data comprises an echosignal power spectrum of a fundamental frequency band (or, again, RF orIQ data from which the echo power signal spectrum may be derived)acquired from the reference phantom using scan settings which areidentical or substantially similar to the second scan settings.

The echo signal power spectra of the fundamental frequency band acquiredfrom volume 140 is normalized by dividing the echo signal power spectraby the fundamental calibration data, resulting in another normalizedspectrum that depends only on the attenuation and backscatter propertiesof the tissues of the ROI and the reference phantom. An AC and a BSC ofthe tissues can also be derived from this normalized spectrum.

According to some embodiments, a non-linearity of the ROI may bedetermined based on the BSC derived from the harmonic frequency banddata and the BSC derived from the fundamental frequency band data. Sucha determination provides improved characterization of the ROI overconventional systems which assume that the non-linearities of thereference phantom and of the ROI are equivalent.

FIG. 2 is a flow diagram of process 200 to determine quantitativeultrasound values according to some embodiments. Process 200 may beexecuted by elements of system 100, but embodiments are not limitedthereto. Process 200 and all other processes mentioned herein may beembodied in processor-executable program code read from one or more ofnon-transitory computer-readable media, such as a hard disk, volatile ornon-volatile random access memory, a DVD-ROM, a Flash drive, and amagnetic tape, and then stored in a compressed, uncompiled and/orencrypted format. In some embodiments, hard-wired circuitry may be usedin place of, or in combination with, program code for implementation ofprocesses according to some embodiments. Embodiments are therefore notlimited to any specific combination of hardware and software.

Initially, at S210, a reference phantom is scanned to acquire RF or IQdata and determine an echo signal power spectra of a fundamentalfrequency band and of a harmonic frequency band therefrom. The referencephantom is scanned used particular scan settings. In some embodiments,additional echo signal power spectra of a fundamental frequency band andof a harmonic frequency band are acquired at S210 using other scansettings.

FIG. 3 illustrates system 300 to perform S210 according to someembodiments. System 300 may be operated by an ultrasound systemprovider, a phantom provider, or other non-clinical entity. Processingunit 312 of ultrasound unit 310 executes a scanning program of storage314 to control transducer 320 to transmit signals to and receive signalsfrom phantom 340. Phantom 340 represents an anticipated ROI (e.g., anadult male torso) and ultrasound unit 310 and transducer 320 maycomprise production-equivalent versions of ultrasound units andtransducers which are anticipated to be used in scanning the anticipatedROI. Storage 314 stores the acquired power spectra.

Next, at S220, the acquired echo signal power spectra of a fundamentalfrequency band and of a harmonic frequency band are stored in anultrasound system. In some embodiments, the stored data comprises datafrom which the echo signal power spectra of a fundamental frequency bandand of a harmonic frequency band may be derived. In some examples, thespectra are stored as the above-described fundamental and harmoniccalibration data of an ultrasound system to be shipped to a customer.According to some embodiments, the spectra are stored in associationwith the scan settings used to acquire the respective spectra.

FIG. 4 is a tabular representation of data stored at S220 according tosome embodiments. Table 400 associates each acquired power spectrum witha reference phantom and scan settings used to acquire the powerspectrum. As shown, more than one type of reference phantom may bescanned at S210. Each reference phantom/scan setting pair is associatedwith fundamental frequency band power spectrum data and harmonicfrequency band power spectrum data. The values of the spectrum datacolumns may consist of filenames of files including the correspondingspectrum data.

In some embodiments, S210 and S220 are performed during a time periodwell before clinical use (e.g., before shipping an ultrasound system toa clinic) of the data acquired therein. Accordingly, the dashed arrowbetween S220 and S230 indicates a passage of time which may besignificantly longer than the time between other adjacent steps ofprocess 200.

At S230, for example in a clinical setting, the ultrasound system inwhich the spectra are stored is operated to acquire echo signal powerspectra of a fundamental frequency band and of a harmonic frequency bandfrom a ROI. The acquisition uses first scan settings which were used togenerate calibration data of a corresponding reference phantom at S210.In some embodiments, the first scan settings are set as default scansettings of the ultrasound system.

According to some embodiments of S230, the ultrasound system transmits asignal with a 3 MHz center frequency and a frequency bandwidth from 2-4MHz. The fundamental signal is then received, in the range of 2-4 MHz.To obtain signals in the harmonic frequency band, a signal istransmitted at a 1.5 MHz center frequency and having a bandwidth between1-2 MHz. The resulting received harmonic signal may exhibit a frequencyband of, e.g., double the center frequency, or between 2-4 MHz.According, subsequent calculations of the QUS values are associated withfrequencies between 2-4 MHz.

Next, at S240, stored calibration data corresponding to the first scansettings is determined. The determined calibration data consists of echosignal power spectra of the fundamental frequency band and the harmonicfrequency band which were acquired using the first scan settings and areference phantom corresponding to the ROI. For example, S240 maycomprise identifying an appropriate reference phantom and scan settingswithin a row of table 400, and acquiring the stored fundamental andharmonic calibration data files identified within the same row of table400.

A first AC and a first BSC are determined at S250. The determination isbased on the echo signal power spectra of the fundamental frequency bandacquired at S230 and the calibration echo signal power spectra of thefundamental frequency band determined at S240. Embodiments are notlimited to the following description of the determination at S250.

Initially, each radio-frequency echo line of the ROI is partitioned intoseveral overlapping time-gated windows. The Fourier Transform is appliedto every window, and the power spectra of the windows that correspond tothe same depth are averaged. The same procedure is performed on thecorresponding ROI of the reference phantom. In standard pulse echoimaging, the measured power spectrum in the fundamental frequency bandof a windowed region in a statistically homogeneous tissue is given byequation (1):S _(s)(f,z)=T(f)E _(tx)(f)E _(rx)(f)D(f,z)(f,z)BSC _(s)(f)e ^(−4α) ^(s)^((f)z)  (1)

The subscript s represents the sample (i.e., the tissue of the ROI). Thedistance from the surface of the transducer to the center of aparticular time-gated window within the ROI is denoted by z. Thefrequency is denoted by f. T(f) represents the transfer function oftransmit pulse. E_(tx)(f) and E_(rx)(f) represents transducerelectro-acoustic and acousto-electric transfer functions, respectively.D(f,z) denotes the effects of diffraction that are related to thetransducer geometry and transmit and receive focusing. α_(s)(f) andBSC_(s)(f) are the frequency-dependent AC and BSC values of the sample,respectively.

Similarly, the power spectrum of the backscattered signal from thereference phantom is:S _(r)(f,z)=T(f)E _(tx)(f)E _(rx)(f)D(f,z)BSC _(r)(f)e ^(−4α) ^(r)^((f)z)  (2)

Dividing the power spectra of the sample by the power spectra of thereference phantom yields:

$\begin{matrix}{{R{S\left( {f,z} \right)}} = {\frac{S_{s}(f)}{S_{r}(f)} = \frac{{{BSC}_{s}(f)}e^{{- 4}{\alpha_{s}(f)}z}}{{{BSC}_{r}(f)}e^{{- 4}{\alpha_{r}(f)}z}}}} & (3)\end{matrix}$

Compensating for the known attenuation and backscatter properties of thereference phantom, equation (3) becomes:RS′(f,z)=BSC _(s)(f)e ^(−4α) ^(r) ^((f)z)  (4)

Computing the natural logarithm yields:ln(RS′(f,z))=ln(BSC _(s)(f))−4α_(s)(f)z  (5)

The attenuation coefficient α_(s)(f) (np/cm) and the backscattercoefficient BSC_(s) (1/cm-str) can then be derived from the slope(−4α_(s)(f)) and intercept (ln (BSC_(s)(f))) of the line that fitsequation (5) versus depth z.

A second AC and a second BSC are determined at S260. The determinationat S260 is based on the echo signal power spectra of the harmonicfrequency band acquired at S230 and the calibration echo signal powerspectra of the harmonic frequency band determined at S240. Embodimentsare not limited to the following description of the determination atS260.

Using the harmonic frequency band to estimate the AC and BSC requiresanew model that accounts for tissue nonlinearity. The second harmonicpressure from a plane wave of P₀ at fundamental frequency f is given by:

$\begin{matrix}{{P_{h}\left( {2f} \right)} = {{{KP}_{0}^{2}(f)}\frac{e^{{- {\alpha_{h}({2f})}}z} - e^{{- 2}{\alpha_{f}(f)}z}}{{2{\alpha_{f}(f)}} - {\alpha_{h}\left( {2f} \right)}}}} & (6)\end{matrix}$where α_(f)(f) and α_(h)(2f) are the attenuation coefficients (np/cm) ofthe fundamental and harmonic signal respectively, and K is a constantthat is proportional to the nonlinearity parameter B/A.

The ratio term in equation (6) can be further simplified using a Taylorseries of the exponential functions:

$\begin{matrix}\begin{matrix}{{P_{h}\left( {2f} \right)} \approx {{{KP}_{0}^{2}(f)}\frac{\left\lbrack {1 - {{\alpha_{h}\left( {2f} \right)}z} + {0.5\left( {{\alpha_{h}\left( {2f} \right)}z} \right)^{2}}} \right\rbrack - \begin{bmatrix}{1 - {2{\alpha_{f}(f)}z} +} \\{0.5\left( {2{\alpha_{f}(f)}z} \right)^{2}}\end{bmatrix}}{{2{\alpha_{f}(f)}} - {\alpha_{h}\left( {2f} \right)}}}} \\{= {{{KP}_{0}^{2}(f)}\frac{\begin{matrix}{{z\left( {{2{\alpha_{f}(f)}} - {\alpha_{h}\left( {2f} \right)}} \right)} -} \\{0.5{z^{2}\left( {{2{\alpha_{f}(f)}} - {\left( {\alpha_{h}\left( {2f} \right)} \right)\left( {{2{\alpha_{f}(f)}} + \left( {\alpha_{h}\left( {2f} \right)} \right)} \right.}} \right.}}\end{matrix}}{{2{\alpha_{f}(f)}} - {\alpha_{h}\left( {2f} \right)}}}} \\{= {{{KP}_{0}^{2}(f)}{z\left\lbrack {1 - {0.5{z\left( {{2{\alpha_{f}(f)}} + \left( {\alpha_{h}\left( {2f} \right)} \right)} \right\rbrack}}} \right.}}} \\{{\approx {{{zKP}_{0}^{2}(f)}e^{{\alpha_{h}({2f})}z}}},}\end{matrix} & (7)\end{matrix}$where the last step uses the common assumption (α_(h)(2f)=2α_(f)(f) andthe Taylor series approximation.

In the case of a focused transmission using a clinical transducer array,P₀(f) is modeled as:P ₀(f)=T(f)E _(tx)(f)D _(tx)(f)  (8)where T(f) is the transfer function of the transmit pulse, E_(tx)(f) isthe electro-mechanical transfer function on transmit, and D_(tx)(f) isthe diffraction patter on transmit. Using equations (7) and (8):P _(h)(2f)=zKT ²(f)E _(tx) ²(f)D _(tx) ²(f)e ^(−4α) ^(h) ⁽² f)z  (9)

The Power Spectrum of the received second harmonic signal is given by:S _(h)(2f)=P _(h) ²(2f)E _(rx) ²(2f)D _(rx) ²(2f)BSC(2f)e ^(−4α) ^(h)^((f)z)  (10)where E_(rx)(f) is the electro-mechanical transfer function on receive,and D_(rx)(f) is the diffraction patter on receive, BSC(2f) is thebackscatter coefficient (np/cm-str) at the second harmonic frequency,and e^(−4α) ^(h) ^((f)z) accounts for the attenuation of returnedharmonic signal.

Combining equations (9) and (10):S _(h)(2f)=[z ² T ⁴(f)E _(tx) ⁴(f)D _(tx) ⁴(f)E _(rx) ²(2f)D _(rx)²(2f)]K ² BSC(2f)e ^(−4α) ^(h) ^((f)z)  (11)

In Tissue Harmonic Imaging (THI) mode, the radio-frequency signals fromtwo pulses 180° out of phase are summed to obtain the harmonic signals.

Each radio-frequency echo line of the ROI is partitioned into severaloverlapping time gated windows. The Fourier Transform is applied toevery window, and the power spectra of the windows that correspond tothe same depth are averaged. The same procedure is performed on thecorresponding ROI of the reference phantom.

The power spectra of the sample and reference in a ROI are given byequation (11). The term in brackets is assumed to be the same for boththe sample and reference. By computing the ratio of the power spectrumfrom the sample and reference we obtain an equation similar to equation(3):

$\begin{matrix}{{{RS}\left( {{2f},z} \right)} = {\frac{S_{h,s}\left( {2f} \right)}{S_{h,r}\left( {2f} \right)} = \frac{K_{s}^{2}{{BSC}_{s}\left( {2f} \right)}e^{{- 4}{\alpha_{s}({2f})}z}}{K_{r}^{2}{{BSC}_{r}\left( {2f} \right)}e^{{- 4}{\alpha_{r}({2f})}z}}}} & (12)\end{matrix}$

Compensating for the known attenuation, backscatter, and nonlinearity ofthe reference phantom, equation (12) becomes:RS′(2f,z)=K _(s) ²(f)BSC _(s)(2f)e ^(−4α) ^(s) ^((f)z)  (13)

Computing the natural logarithm yields:ln(RS′ ^((2f,z)))=ln(K _(s) ²)+ln(BSC _(s)(2f))−4α_(s)(2f)z  (14)

The attenuation coefficient α_(s) (dB/cm) at frequency 2f can be derivedfrom the slope of the line that fits equation (14) versus depth z. Theintercept of the line that fits equation (14) versus depth z yields ln(BSC_(s)(2f) biased by the nonlinearity term ln (K_(s) ²).

Returning to process 200, a non-linearity of the ROI is determined atS270 based on the first BSC determined at S250 and the second BSCdetermined at S260. Continuing with the above example, the non-linearityterm ln (K_(s) ²) in equation (14) can be estimated by measuring the ln(BSC_(s) (2f)) using the fundamental frequency band based on equation(5), where the fundamental frequency is now 2f, and substituting theresult into equation (14).

An image of the ROI is generated and displayed at S280. The image may begenerated based on one or both of the spectra acquired at S230 as isknown in the art. The image may also indicate the non-linearity and anyother values determined based on the received signals.

FIG. 5 shows image 500 generated and displayed at S280 according to someembodiments. As shown, determined values shear wave speed (Vs),Elasticity (E), AC, BSC, ultrasonically-derived fat fraction (UDFF) andnon-linearity (K) are displayed contemporaneously with ultrasound B-modeimage data. These quantitative measurements may improve the diagnosticcapability of medical ultrasound by removing the qualitativeinterpretation of B-mode images, and by reducing system-dependentfactors.

The estimates of the AC based on the fundamental band and the harmonicband should be equivalent. Accordingly, image 500 may display eitherestimate or an average of the two. In some embodiments, variability maybe reduced by determining and displaying a weighted average of the twoAC estimates.

In the case of the BSC, the BSC value determined at S260 based on theharmonic band is biased by the nonlinearity term. Therefore, the BSCdisplayed at S280 may be the BSC value determined at S250 based on thefundamental band. If the nonlinearity term is assumed to be negligible,then an average of the two BSC values may be displayed.

FIG. 6 is a block diagram of ultrasound imaging system 600 according tosome embodiments. System 600 may implement one or more of the processesdescribed herein.

System 600 is a phased-array ultrasound imaging system, but embodimentsare not limited thereto. Typical phased array systems utilize 64 to 256receive channels and a comparable number of transmit channels. Forclarity, FIG. 6 illustrates a single transmit-and-receive channel.

System 600 comprises transducer element 605 and transmit/receive switch610. Transducer element 605 may comprise an element of a 1-, 1.25-,1.5-, 1.75- or 2-dimensional array of piezoelectric or capacitivemembrane elements. Transmit/receive switch 610 is operated to eitherallow transmission of ultrasonic energy via element 605 (e.g., inresponse to application of a voltage across element 605), or to allowreception of a voltage generated by element 605 in response to receivedultrasonic energy (i.e., echoes).

Transmit beamformer 615 is operable, in conjunction withdigital-to-analog converter 620 and high-voltage transmitter 625, togenerate waveforms for a plurality of channels, where each waveform mayexhibit a different amplitude, delay, and/or phase. Receive beamformer630 receives signals from a plurality of channels, each of which may besubjected to amplification 635, filtering 640, analog-to-digitalconversion 645, delays and/or phase rotators, and one or more summers.Receive beamformer 630 may be configured by hardware or software toapply relative delays, phases, and/or apodization to form one or morereceive beams in response to each transmit beam. Receive beamformer 630may provide dynamic receive focusing as is known in the art, as well asfixed focus reception.

The receive beams formed by receive beamformer 630 represent thematerial through which the transmit beams and receive beams have passed.The receive beams are output to processor 650 for processing. Forexample, processor 650 may generate images based on the receive beams.

Processor 650 may execute processor-executable program code stored inmemory 660 to perform and/or to control other components of system 600to perform the processes described herein. Processor 650 may comprise aB-mode detector, Doppler detector, pulsed wave Doppler detector,correlation processor, Fourier transform processor, application specificintegrated circuit, general processor, control processor, imageprocessor, field programmable gate array, digital signal processor,analog circuit, digital circuit, combinations thereof, or othercurrently-known or later-developed device for generating data (e.g.,image data) based on beamformed ultrasound samples.

Memory 660 may comprise a non-transitory computer readable storage mediasuch as Random Access Memory and/or non-volatile memory (e.g., Flashmemory, hard disk memory). Memory 660 may store program code,calibration data, B-mode images, and/or any other suitable data. Display655 may comprise a cathode ray tube display, liquid crystal display,light-emitting diode display, plasma display, or other type of displayfor displaying images and/or measured values.

Those in the art will appreciate that various adaptations andmodifications of the above-described embodiments can be configuredwithout departing from the scope and spirit of the claims. Therefore, itis to be understood that the claims may be practiced other than asspecifically described herein.

What is claimed is:
 1. An ultrasound system comprising: a memory storingan echo signal power spectrum of a reference phantom for a fundamentalfrequency band and an echo signal power spectrum of the referencephantom for a harmonic frequency band, wherein a center frequency of theharmonic frequency band is substantially similar to a center frequencyof the fundamental frequency band; a transducer to: transmit firstultrasound beams into a region of tissue and receive first acousticradio-frequency signals representing an echo signal power spectrum ofthe region of tissue for the fundamental frequency band; and transmitsecond ultrasound beams into the region of tissue and receive secondacoustic radio-frequency signals representing an echo signal powerspectrum of the region of tissue for the harmonic frequency band; aprocessing unit to: determine a first backscatter coefficient based onthe echo signal power spectrum of the region of tissue for thefundamental frequency band and the echo signal power spectrum of thereference phantom for the fundamental frequency band; determine a valuerepresenting a second backscatter coefficient and a non-linearity termassociated with the region of tissue based on the echo signal powerspectrum of the region of tissue for the harmonic frequency band and theecho signal power spectrum of the reference phantom for the harmonicfrequency band; and determine the non-linearity term associated with theregion of tissue based on the first backscatter coefficient and thevalue; and a display to display the second backscatter coefficient, thenon-linearity term, and a B-mode image of the region of tissue.
 2. Anultrasound system according to claim 1, wherein the echo signal powerspectrum of the reference phantom for the fundamental frequency band andthe echo signal power spectrum of the region of tissue for thefundamental frequency band were acquired using substantially similarscan settings.
 3. An ultrasound system according to claim 2, wherein theecho signal power spectrum of the reference phantom for the harmonicfrequency band and the echo signal power spectrum of the region oftissue for the harmonic frequency band were acquired using substantiallysimilar scan settings.
 4. A system according to claim 1, the memorystoring an echo signal power spectrum of a second reference phantom forthe fundamental frequency band and an echo signal power spectrum of thesecond reference phantom for the harmonic frequency band, and theprocessing unit further to determine to use the echo signal powerspectrum of the reference phantom for the fundamental frequency band forthe determination of the first backscatter coefficient and the echosignal power spectrum of the reference phantom for the harmonicfrequency band for the determination of the second backscattercoefficient, based on a correlation between the region of tissue and thereference phantom.
 5. A system according to claim 4, the echo signalpower spectrum of the reference phantom for the fundamental frequencyband and the echo signal power spectrum of the reference phantom for theharmonic frequency band having been acquired using first scan settings,the memory storing a second echo signal power spectrum of the referencephantom for the fundamental frequency band and a second echo signalpower spectrum of the reference phantom for the harmonic frequency band,the second echo signal power spectrum acquired using second scansettings, wherein the echo signal power spectrum of the region of tissuefor the fundamental frequency band and the echo signal power spectrum ofthe region of tissue for the harmonic frequency band are acquired usingthird scan settings, and wherein the processing unit is to determine touse the echo signal power spectrum of the reference phantom for thefundamental frequency band and the echo signal power spectrum of thereference phantom for the harmonic frequency band for the determinationof the first backscatter coefficient and the determination of the secondbackscatter coefficient, based on a correlation between the first scansettings and the third scan settings.
 6. A system according to claim 1,the processing unit further to: determine an attenuation coefficient ofthe region of tissue based on the echo signal power spectrum of theregion of tissue for the harmonic frequency band, the echo signal powerspectrum of the reference phantom for the harmonic frequency band, andan attenuation coefficient of the reference phantom.
 7. A systemaccording to claim 6, further comprising: the display to simultaneouslydisplay the second backscatter coefficient, the attenuation coefficientof the region of tissue, the non-linearity term, and the B-mode image ofthe region of tissue.
 8. A method comprising: controlling an ultrasoundsystem transducer to acquire an echo signal power spectrum of a regionof tissue for a fundamental frequency band and an echo signal powerspectrum of the region of tissue for a harmonic frequency band, whereina center frequency of the harmonic frequency band is substantiallysimilar to a center frequency of the fundamental frequency band;determining a first backscatter coefficient based on the echo signalpower spectrum of the region of tissue for a fundamental frequency bandand an echo signal power spectrum of a reference phantom for thefundamental frequency band; determining a value representing a secondbackscatter coefficient and a non-linearity term associated with theregion of tissue based on the echo signal power spectrum of the regionof tissue for the harmonic frequency band and an echo signal powerspectrum of the reference phantom for the harmonic frequency band;determining the non-linearity term associated with the region of tissuebased on the first backscatter coefficient and the value; and displayingthe second backscatter coefficient, the non-linearity term, and a B-modeimage of the region of tissue.
 9. A method according to claim 8, whereinthe echo signal power spectrum of the reference phantom for thefundamental frequency band and the echo signal power spectrum of theregion of tissue for the fundamental frequency band are acquired usingsubstantially similar scan settings.
 10. A method according to claim 9,wherein the echo signal power spectrum of the reference phantom for theharmonic frequency band and the echo signal power spectrum of the regionof tissue for the harmonic frequency band were acquired usingsubstantially similar scan settings.
 11. A method according to claim 8,further comprising: storing an echo signal power spectrum of a secondreference phantom for the fundamental frequency band and an echo signalpower spectrum of the second reference phantom for the harmonicfrequency band, and determining to use the echo signal power spectrum ofthe reference phantom for the fundamental frequency band for thedetermination of the first backscatter coefficient and the echo signalpower spectrum of the reference phantom for the harmonic frequency bandfor the determination of the second backscatter coefficient, based on acorrelation between the region of tissue and the reference phantom. 12.A method according to claim 11, the echo signal power spectrum of thereference phantom for the fundamental frequency band and the echo signalpower spectrum of the reference phantom for the harmonic frequency bandhaving been acquired using first scan settings, further comprising:storing a second echo signal power spectrum of the reference phantom forthe fundamental frequency band and the second echo signal power spectrumof the reference phantom for a harmonic frequency band, the second echosignal power spectrum acquired using second scan settings, wherein theecho signal power spectrum of a region of tissue for the fundamentalfrequency band and the echo signal power spectrum of the region oftissue for the harmonic frequency band are acquired using third scansettings, and further comprising determining to use the echo signalpower spectrum of the reference phantom for the fundamental frequencyband for the determination of the first backscatter coefficient and theecho signal power spectrum of the reference phantom for the harmonicfrequency band for the determination of the second backscattercoefficient, based on a correlation between the first scan settings andthe third scan settings.
 13. A method according to claim 8, furthercomprising: determining an attenuation coefficient of the region oftissue based on the echo signal power spectrum of the region of tissuefor the harmonic frequency band, the echo signal power spectrum of thereference phantom for the harmonic frequency band, and an attenuationcoefficient of the reference phantom.
 14. A method according to claim13, further comprising: simultaneously displaying the second backscattercoefficient, the attenuation coefficient of the region of tissue, thenon-linearity term, and the B-mode image of the region of tissue.
 15. Anultrasound imaging system comprising: a transducer to acquire an echosignal power spectrum of a region of tissue for a fundamental frequencyband and an echo signal power spectrum of the region of tissue for aharmonic frequency band, wherein a center frequency of the harmonicfrequency band is substantially similar to a center frequency of thefundamental frequency band; a processing unit to: determine a firstbackscatter coefficient based on the echo signal power spectrum of theregion of tissue for the fundamental frequency band and an echo signalpower spectrum of a reference phantom for the fundamental frequencyband; determine a value representing a second backscatter coefficientand a non-linearity term associated with the region of tissue based onthe echo signal power spectrum of the region of tissue for the harmonicfrequency band and an echo signal power spectrum of the referencephantom for the harmonic frequency band; and determine the non-linearityterm associated with the region of tissue based on the first backscattercoefficient and the value; and a display to display the secondbackscatter coefficient, the non-linearity term, and a B-mode image ofthe region of tissue.
 16. A system according to claim 15, wherein theecho signal power spectrum of the reference phantom for the fundamentalfrequency band and the echo signal power spectrum of the region oftissue for the fundamental frequency band are acquired usingsubstantially similar scan settings.
 17. A system according to claim 15,the processing unit to determine to use the echo signal power spectrumof the reference phantom for the fundamental frequency band for thedetermination of the first backscatter coefficient and the echo signalpower spectrum of the reference phantom for the harmonic frequency bandfor the determination of the second backscatter coefficient, based on acorrelation between the region of tissue and the reference phantom. 18.A system according to claim 17, wherein the echo signal power spectrumof the reference phantom for the fundamental frequency band and the echosignal power spectrum of the reference phantom for the harmonicfrequency band are acquired using first scan settings, wherein the echosignal power spectrum of a region of tissue for the fundamentalfrequency band and the echo signal power spectrum of the region oftissue for the harmonic frequency band are acquired using second scansettings, and wherein the processing unit is to determine to use theecho signal power spectrum of the reference phantom for the fundamentalfrequency band for the determination of the first backscattercoefficient and the echo signal power spectrum of the reference phantomfor the harmonic frequency band for the determination of the secondbackscatter coefficient, based on a correlation between the first scansettings and the second scan settings.